WO2015115320A1 - 医療用画像形成装置 - Google Patents

医療用画像形成装置 Download PDF

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Publication number
WO2015115320A1
WO2015115320A1 PCT/JP2015/051809 JP2015051809W WO2015115320A1 WO 2015115320 A1 WO2015115320 A1 WO 2015115320A1 JP 2015051809 W JP2015051809 W JP 2015051809W WO 2015115320 A1 WO2015115320 A1 WO 2015115320A1
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Prior art keywords
image
observation
laser
light
laser light
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PCT/JP2015/051809
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English (en)
French (fr)
Japanese (ja)
Inventor
宏幸 亀江
伊藤　毅
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オリンパス株式会社
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Priority to EP15742832.7A priority Critical patent/EP3100670A4/en
Priority to CN201580006447.2A priority patent/CN105939651B/zh
Publication of WO2015115320A1 publication Critical patent/WO2015115320A1/ja
Priority to US15/221,664 priority patent/US10226168B2/en

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B1/00—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor
    • A61B1/00002—Operational features of endoscopes
    • A61B1/00004—Operational features of endoscopes characterised by electronic signal processing
    • A61B1/00009—Operational features of endoscopes characterised by electronic signal processing of image signals during a use of endoscope
    • A61B1/000094—Operational features of endoscopes characterised by electronic signal processing of image signals during a use of endoscope extracting biological structures
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B1/00—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor
    • A61B1/04—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor combined with photographic or television appliances
    • A61B1/043—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor combined with photographic or television appliances for fluorescence imaging
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B1/00—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor
    • A61B1/06—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor with illuminating arrangements
    • A61B1/0638—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor with illuminating arrangements providing two or more wavelengths
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B1/00—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor
    • A61B1/06—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor with illuminating arrangements
    • A61B1/0655—Control therefor
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B1/00—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor
    • A61B1/06—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor with illuminating arrangements
    • A61B1/0661—Endoscope light sources
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B1/00—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor
    • A61B1/06—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor with illuminating arrangements
    • A61B1/0661—Endoscope light sources
    • A61B1/0669—Endoscope light sources at proximal end of an endoscope
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B1/00—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor
    • A61B1/313—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor for introducing through surgical openings, e.g. laparoscopes
    • A61B1/3137—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor for introducing through surgical openings, e.g. laparoscopes for examination of the interior of blood vessels
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue
    • A61B5/1455—Measuring characteristics of blood in vivo, e.g. gas concentration or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue using optical sensors, e.g. spectral photometrical oximeters
    • A61B5/14551—Measuring characteristics of blood in vivo, e.g. gas concentration or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue using optical sensors, e.g. spectral photometrical oximeters for measuring blood gases
    • A61B5/14552—Details of sensors specially adapted therefor
    • G—PHYSICS
    • G02—OPTICS
    • G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
    • G02B23/00—Telescopes, e.g. binoculars; Periscopes; Instruments for viewing the inside of hollow bodies; Viewfinders; Optical aiming or sighting devices
    • G02B23/24—Instruments or systems for viewing the inside of hollow bodies, e.g. fibrescopes
    • G02B23/2407—Optical details
    • G02B23/2461—Illumination
    • G—PHYSICS
    • G02—OPTICS
    • G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
    • G02B23/00—Telescopes, e.g. binoculars; Periscopes; Instruments for viewing the inside of hollow bodies; Viewfinders; Optical aiming or sighting devices
    • G02B23/24—Instruments or systems for viewing the inside of hollow bodies, e.g. fibrescopes
    • G02B23/2476—Non-optical details, e.g. housings, mountings, supports
    • G02B23/2484—Arrangements in relation to a camera or imaging device
    • G—PHYSICS
    • G03—PHOTOGRAPHY; CINEMATOGRAPHY; ANALOGOUS TECHNIQUES USING WAVES OTHER THAN OPTICAL WAVES; ELECTROGRAPHY; HOLOGRAPHY
    • G03B—APPARATUS OR ARRANGEMENTS FOR TAKING PHOTOGRAPHS OR FOR PROJECTING OR VIEWING THEM; APPARATUS OR ARRANGEMENTS EMPLOYING ANALOGOUS TECHNIQUES USING WAVES OTHER THAN OPTICAL WAVES; ACCESSORIES THEREFOR
    • G03B15/00—Special procedures for taking photographs; Apparatus therefor
    • G03B15/02—Illuminating scene
    • G03B15/03—Combinations of cameras with lighting apparatus; Flash units
    • G03B15/05—Combinations of cameras with electronic flash apparatus; Electronic flash units
    • G—PHYSICS
    • G06—COMPUTING OR CALCULATING; COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T5/00—Image enhancement or restoration
    • G06T5/90—Dynamic range modification of images or parts thereof
    • G06T5/92—Dynamic range modification of images or parts thereof based on global image properties
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B1/00—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor
    • A61B1/06—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor with illuminating arrangements
    • A61B1/063—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor with illuminating arrangements for monochromatic or narrow-band illumination
    • G—PHYSICS
    • G03—PHOTOGRAPHY; CINEMATOGRAPHY; ANALOGOUS TECHNIQUES USING WAVES OTHER THAN OPTICAL WAVES; ELECTROGRAPHY; HOLOGRAPHY
    • G03B—APPARATUS OR ARRANGEMENTS FOR TAKING PHOTOGRAPHS OR FOR PROJECTING OR VIEWING THEM; APPARATUS OR ARRANGEMENTS EMPLOYING ANALOGOUS TECHNIQUES USING WAVES OTHER THAN OPTICAL WAVES; ACCESSORIES THEREFOR
    • G03B2215/00—Special procedures for taking photographs; Apparatus therefor
    • G03B2215/05—Combinations of cameras with electronic flash units
    • G03B2215/0564—Combinations of cameras with electronic flash units characterised by the type of light source
    • G03B2215/0567—Solid-state light source, e.g. LED, laser
    • G—PHYSICS
    • G06—COMPUTING OR CALCULATING; COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T2207/00—Indexing scheme for image analysis or image enhancement
    • G06T2207/10—Image acquisition modality
    • G06T2207/10068—Endoscopic image
    • G—PHYSICS
    • G06—COMPUTING OR CALCULATING; COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T2207/00—Indexing scheme for image analysis or image enhancement
    • G06T2207/20—Special algorithmic details
    • G06T2207/20172—Image enhancement details
    • G06T2207/20208—High dynamic range [HDR] image processing
    • G—PHYSICS
    • G06—COMPUTING OR CALCULATING; COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T2207/00—Indexing scheme for image analysis or image enhancement
    • G06T2207/30—Subject of image; Context of image processing
    • G06T2207/30004—Biomedical image processing
    • G06T2207/30101—Blood vessel; Artery; Vein; Vascular

Definitions

  • the present invention relates to a medical image forming apparatus.
  • solid light sources Compared to conventional gas light sources, solid light sources have advantages such as low power consumption, high connection efficiency, small size, and high-speed switching. The technological innovation for such solid state light sources is remarkable.
  • a solid-state laser has a characteristic that the light density in the emission area is extremely high. Due to this characteristic, so-called fiber light sources configured by combining a solid-state laser with, for example, an optical fiber have been actively developed.
  • the fiber light source is suitable for illuminating the inside of a thin structure, and its application to an endoscope or the like is being advanced.
  • Japanese Patent Application Laid-Open No. 2011-200572 discloses a white blood image, a fine blood vessel image, an oxygen saturation image, and a blood vessel depth image.
  • An electronic endoscope system capable of simultaneously acquiring and displaying one or two types of images selected by a user or the like is provided.
  • a plurality of solid-state light sources for broadband light, a plurality of lasers for microvascular images, a plurality of lasers for oxygen saturation images, and a plurality of lasers for blood vessel depth images Is provided as a light source.
  • Japanese Patent Application Laid-Open No. 2011-200572 acquires a plurality of images by irradiating a target object with a plurality of light sources corresponding to selected images simultaneously or sequentially.
  • the present invention has been made in view of the above circumstances, and an object thereof is to provide a medical image forming apparatus with high image reproduction accuracy while realizing low cost, low volume, and low power consumption.
  • a medical image forming apparatus includes a plurality of laser light emitting elements that emit laser beams having different wavelengths, an image selection unit for selecting the type of observation image, A light source control unit that performs lighting control of the plurality of laser light emitting elements according to an observation mode corresponding to the selected combination of observation images, and imaging that images the return light of the laser light from the observation target and outputs it as an image signal And an image signal processing circuit that forms the observation image from the image signal from the imaging unit, and is turned on by the light source control unit when the type of the selected observation image is the first observation image
  • Laser light emitting element for emitting a laser beam are included.
  • FIG. 1 is a graph showing the results of calculating the average color rendering index Ra for various wavelengths and the number of lasers.
  • FIG. 2A is a diagram schematically showing a cross-sectional structure of a biological mucous membrane.
  • FIG. 2B is a diagram schematically illustrating the relationship between the wavelength length and the penetration depth.
  • FIG. 3 is a diagram showing the wavelength dependence of the extinction coefficient of blood hemoglobin.
  • FIG. 4A is a graph showing absorption intensity characteristics regarding the autofluorescent material.
  • FIG. 4B is a graph showing fluorescence intensity characteristics.
  • FIG. 5 is a block diagram showing the configuration of the medical image forming apparatus according to the first embodiment of the present invention.
  • FIG. 5 is a block diagram showing the configuration of the medical image forming apparatus according to the first embodiment of the present invention.
  • FIG. 6 is a diagram illustrating an example of laser output conditions when all of the special light image 1, the special light image 2, the special light image 3, and the white light image are selected.
  • FIG. 7 is a diagram illustrating an example of laser output conditions when special light images 1, 2, and 3 and a white light image are displayed simultaneously.
  • FIG. 8 is a diagram illustrating an example of parallel display of four observation images.
  • FIG. 9 is a diagram illustrating an example of laser output conditions when only the special light image 1 and the white light image are selected.
  • FIG. 10 is a diagram illustrating an example of parallel display of two observation images.
  • FIG. 11 is a block diagram showing a configuration of a medical image forming apparatus according to the second embodiment of the present invention.
  • FIG. 12 is a diagram illustrating an example of laser output conditions when all of the special light image 1 and the white light image are selected in the second embodiment of the present invention.
  • FIG. 13 is a diagram illustrating an example of parallel display of two observation images according to the second embodiment of the present invention.
  • the applicant performed calculation of the average color rendering index Ra, which is one of the illuminator quality evaluation parameters defined in Japanese Industrial Standards (JIS), for various wavelengths and the number of lasers. As a result, as shown in FIG. 1, it has been found that by combining a plurality of laser beams having different wavelengths, a performance equivalent to or higher than the broad spectrum general illumination conventionally used can be obtained. It was. Specifically, if there are at least four lasers, the average color rendering index Ra is 80, and sufficient performance as an illumination light source can be obtained.
  • JIS Japanese Industrial Standards
  • the laser can output light with high light density and parallelism from a light emitting area smaller than a gas light source or LED. Therefore, a laser as a light source for white light observation that requires color rendering is introduced with high efficiency into a small-diameter light guide member such as a fiber in an observation apparatus that is expected to be observed in a closed space such as an endoscope apparatus. Easy to use (low power consumption, high brightness lighting). In addition, for special light observations that have been actively developed in the field of endoscopes in recent years, the narrow spectral characteristics of the laser also provide the advantage of easily acquiring the wavelength characteristics of specific substances at the target site. be able to. Special light observation includes, for example, observation of a blood vessel enhancement image, an oxygen saturation image, and an autofluorescence image. Hereinafter, each observation image will be described.
  • wavelength light (B light) having a short wavelength penetrates only to the vicinity of the surface layer, and is absorbed and scattered in the vicinity thereof.
  • the return light at this time is emitted from the surface of the living body.
  • the wavelength light (G light) having a medium wavelength penetrates to a range deeper than the surface layer, and is absorbed and scattered in the vicinity thereof.
  • the return light at this time is emitted from the surface of the living body. With this return light, it is possible to acquire information in a deeper part than light having a short wavelength.
  • wavelength light (R light) having a long wavelength (on the order of 600 nm) penetrates to a deeper range and is absorbed and scattered in the vicinity thereof.
  • the return light at this time is emitted from the surface of the living body. With this return light, it is possible to acquire information in a deeper part than light having a medium wavelength.
  • FIG. 3 shows the wavelength dependence of the extinction coefficient of blood hemoglobin. As shown in FIG. 3, the absorption spectra are slightly different between oxygenated hemoglobin and reduced hemoglobin. When light of the first half wavelength of the 400nm range, which has a high hemoglobin extinction coefficient, is irradiated toward the living body, it is possible to obtain an image that emphasizes the blood vessels that are mainly present on the surface of the living body.
  • Oxygen saturation image The oxygen saturation of hemoglobin is calculated by obtaining the amount of oxyhemoglobin relative to the amount of total hemoglobin.
  • the wavelengths of 450 nm, 540 nm, and 805 nm are wavelengths with almost no difference in extinction coefficient between oxyhemoglobin and reduced hemoglobin.
  • wavelengths of 430 nm, 560 nm, and 760 nm are wavelengths having a larger extinction coefficient of reduced hemoglobin
  • wavelengths of 470 nm, 590 nm, and 840 nm are wavelengths having a greater extinction coefficient of oxyhemoglobin.
  • the image information of each wavelength band thus obtained is assigned to, for example, each color of red, green, and blue.
  • an observation image is an oxygen saturation image.
  • the light penetration length is longer for longer wavelengths, so when using light with a wavelength in the 400 nm range, the oxygen saturation image for the surface blood vessels is used with light having a wavelength in the 500 nm range.
  • FIG. 4A is a graph showing the absorption intensity characteristic regarding the autofluorescent substance
  • FIG. 4B is a graph showing the fluorescence intensity characteristic.
  • These graphs show absorption intensity characteristics and fluorescence intensity characteristics of Flavin Adenine Dinucleotide (FAD) and porphyrin, which are autofluorescent substances correlated with tumors.
  • FAD Flavin Adenine Dinucleotide
  • porphyrin generates fluorescence by light having a central wavelength of 400 nm
  • FAD generates fluorescence by light having central wavelengths of 380 nm and 450 nm.
  • An image obtained by imaging such fluorescence is an autofluorescence image.
  • the fluorescence intensity of autofluorescence differs between the lesioned part and the normal part. That is, fluorescence having a peak near 550 nm is generated in the normal part, while fluorescence having two peaks of 560 nm and 630 nm is generated in the lesion site. It is known that porphyrin accumulates in lesions such as cancer. Therefore, the fluorescence at 630 nm for the lesion site shown in FIG. 4B is fluorescence derived from porphyrin.
  • FIG. 5 is a block diagram showing the configuration of the medical image forming apparatus according to the first embodiment of the present invention.
  • the medical image forming apparatus 100 displays a special light image 1, a special light image 2, a special light image 3, and a white light image with high image accuracy.
  • the special light image is an observation image obtained by irradiating with light of a specific wavelength, in which specific features of the observation target are emphasized.
  • An example of the special light image 1 is an autofluorescence image.
  • the special light image 2 of an example is a blood vessel emphasis image.
  • the special light image 3 as an example is an oxygen saturation image.
  • the white light image is a normal observation image obtained by irradiating with white light, in which specific features of the observation target are not emphasized. This white light image is used for screening or the like.
  • the medical image forming apparatus 100 shown in FIG. 5 has laser light emitting elements (hereinafter simply referred to as lasers) 1 to 7 as illumination light sources.
  • lasers are, for example, semiconductor lasers and have different emission wavelengths.
  • laser 1 emits light with a wavelength of 400 nm
  • laser 2 emits light with a wavelength of 450 nm
  • laser 3 emits light with a wavelength of 420 nm
  • laser 4 emits light with a wavelength of 540 nm.
  • the laser 5 emits light of 640 nm
  • the laser 6 emits light of 590 nm
  • the laser 7 emits light of 560 nm.
  • Lasers 1 to 7 are connected to the light source control unit 8.
  • the light source control unit 8 is connected to the image selection unit 9 and the observation mode storage unit 10.
  • the image selection unit 9 is an operation member such as a touch panel, for example, and accepts an operation for selecting the type of observation image by the user.
  • the observation mode storage unit 10 stores laser output conditions (laser lighting start timing, lighting period, lighting cycle, etc.) for each observation mode suitable for the combination of observation images selected by the image selection unit 9.
  • the light source control unit 8 acquires the laser output condition corresponding to the observation mode from the observation mode storage unit 10 and forms the observation image selected by the image selection unit 9 in accordance with the acquired laser output condition. Control lighting. Details will be described later.
  • Examples of laser output conditions when all of special light image 1 (autofluorescence image), special light image 2 (blood vessel enhancement image), special light image 3 (oxygen saturation image), and white light image are selected.
  • This laser output condition is a laser output condition for an observation mode in which four selected observation images are displayed simultaneously.
  • the image display cycle is 1 frame
  • 1/4 frame is a period for forming the special light image 1
  • the lasers 1 and 2 are turned on during this period.
  • the 2/4 frame is a period for forming the special light image 2
  • the lasers 3, 4, and 5 are turned on during this period.
  • the 3/4 frame is a period for forming the special light image 3, and the lasers 6 and 7 are turned on during this period.
  • the 4/4 frame is a period for forming a white light image, and the lasers 2, 4, 5, and 6 are turned on during this period.
  • the laser used for forming the special light image is also used for forming the white light image. For this reason, the number of lasers may be seven.
  • the lasers 1 to 7 are connected to the combiner 12 via the optical fiber 11.
  • the combiner 12 combines a plurality of laser beams guided by the optical fiber 11.
  • the combiner 12 is connected to a light distribution conversion member 16 provided at the distal end of the scope insertion portion 14 via an optical fiber 13.
  • the light distribution conversion member 16 adjusts the light distribution of the mixed light guided by the optical fiber 13 to a state suitable for imaging (for example, an optimal light distribution spread angle) and emits the light toward an observation target (not shown).
  • the light distribution conversion member 16 is, for example, a lens, a surface diffusing member having a light diffusing function on the surface, an internal diffusing member containing a minute member having a different refractive index or reflectance, or a combination thereof.
  • a composite optical member is desirable.
  • the imaging unit 18 includes, for example, R (red), G (green), and B (blue) imaging elements (for example, CCD imaging elements) that are regularly arranged on the same plane.
  • the R image sensor is an image sensor having a sensitivity peak in the R wavelength band (near 600 nm).
  • the G image sensor is an image sensor having a sensitivity peak in the G wavelength band (near 540 nm).
  • the B image sensor is an image sensor having a peak of sensitivity in the B wavelength band (around 480 nm).
  • Each of these imaging elements generates light-specific image signals by photoelectrically converting light in the corresponding wavelength band.
  • the illumination imaging synchronization unit 20 is connected to the imaging unit 18.
  • the illumination imaging synchronization unit 20 is also connected to the light source control unit 8 and the image distribution unit 22.
  • the illumination imaging synchronization unit 20 synchronizes illumination by the lasers 1 to 7, imaging by the imaging unit 18, and image distribution by the image distribution unit 22, so that the light source control unit 8, the imaging unit 18, and the image distribution unit 22 are synchronized. And a sync signal is output.
  • the imaging unit 18 is connected to the image distribution unit 22.
  • the image distribution unit 22 includes a plurality of image forming units provided in the image signal processing circuit 24, that is, a special light 1 image forming unit 24a, a special light 2 image forming unit 24b, a special light 3 image forming unit 24c, and white light. It is connected to each of the image forming units 24d.
  • the image distribution unit 22 transmits the image signal received from the imaging unit 18 to the corresponding image forming unit in response to the input of the synchronization signal from the illumination imaging synchronization unit 20.
  • the special light 1 image forming unit 24a forms a special light image 1 (autofluorescence image) from the received image signal.
  • the special light 2 image forming unit 24b forms the special light image 2 (blood vessel emphasized image) from the received image signal.
  • the special light 3 image forming unit 24c forms a special light image 3 (oxygen saturation image) from the received image signal.
  • the white light image forming unit 24d forms a white light image from the received image signal.
  • the image display unit 26 receives the observation image formed by the image forming unit of the image signal processing circuit 24 and displays it in a state that is easy for the user or the like to understand. For example, the image display unit 26 divides one screen into four and displays each observation image in parallel.
  • the brightness correction unit 28 receives the observation image from the image display unit 26 and determines the brightness of the observation image displayed on the image display unit 26. Then, when the brightness of the observation image displayed on the image display unit 26 is not appropriate, a correction signal is output to the light source control unit 8 so that the brightness of the observation image becomes appropriate.
  • an observation image is selected by an operation of the image selection unit 9 by the user.
  • the light source control unit 8 acquires a laser output condition corresponding to the observation mode suitable for the selected observation image from the observation mode storage unit 10.
  • FIG. 7 shows an example of laser output conditions when the special light images 1, 2, and 3 and the white light image are displayed simultaneously.
  • the laser 1 is used only for forming the special light image 1 (autofluorescence image). Therefore, the lighting start timing of the laser 1 is the start timing of 1/4 frame, which is the formation period of the special light image 1.
  • the lighting period of the laser 1 is a quarter of one frame. Further, the lighting cycle is a period of one frame.
  • the laser 2 is used for forming the special light image 1 and the white light image. Therefore, the lighting start timing of the laser 2 is the start timing of 1/4 frame, which is the formation period of the special light image 1, and the start timing of 4/4 frame, which is the formation period of the white light image.
  • the 4/4 frame and the 1/4 frame are continuous. Therefore, the actual lighting start timing of the laser 2 is the start timing of the 1/4 frame and the start timing of the 4/4 frame only for the first frame, and the start timing of the 4/4 frame in the previous frame after the second frame It is.
  • the lighting period of the laser 2 is a quarter period of one frame only for the first quarter frame, and is a half period of one frame thereafter. Further, the lighting cycle of the laser 2 is a period of 3/4 of one frame only during the period from the first frame 1/4 to the frame 4/4, and thereafter is a period of one frame.
  • the laser 3 is used only for forming the special light image 2 (blood vessel enhanced image). Therefore, the lighting start timing of the laser 3 is a start timing of 2/4 frame, which is the formation period of the special light image 2.
  • the lighting period of the laser 3 is a quarter period of one frame. Further, the lighting cycle is a period of one frame.
  • the laser 4 is used to form the special light image 2 and the white light image.
  • the lighting start timing of the laser 4 is the start timing of the 2/4 frame that is the formation period of the special light image 2 and the start timing of the 4/4 frame that is the formation period of the white light image.
  • the lighting period of the laser 4 is a quarter of one frame.
  • the lighting cycle is a period of 1/2 frame.
  • the laser 5 is used to form the special light image 2 and the white light image. Therefore, the lighting start timing of the laser 5 is the start timing of 2/4 frame, which is the formation period of the special light image 2, and the start timing of 4/4 frame, which is the formation period of the white light image.
  • the lighting period of the laser 5 is a quarter of one frame. Further, the lighting cycle is a period of 1/2 frame.
  • the laser 6 is used for forming a special light image 3 (oxygen saturation image) and a white light image. Therefore, the lighting start timing of the laser 6 is the start timing of the 3/4 frame that is the formation period of the special light image 3 and the start timing of the 4/4 frame that is the formation period of the white light image. Since the 3/4 frame and the 4/4 frame are continuous, the actual lighting start timing of the laser 6 is the start timing of the 3/4 frame.
  • the lighting period of the laser 6 is a half period of one frame. Further, the lighting cycle is a period of one frame.
  • the laser 7 is used only for forming the special light image 3. Accordingly, the lighting start timing of the laser 7 is the start timing of the 3/4 frame that is the formation period of the special light image 3.
  • the lighting period of the laser 7 is a quarter of one frame. Further, the lighting cycle is a period of one frame.
  • the light source control unit 8 turns on the lasers 1 to 7 in accordance with the output conditions as described above and the synchronization signal from the illumination imaging synchronization unit 20.
  • the imaging unit 18 images the return light from the observation target of the laser light emitted from the lasers 1 to 7 in accordance with the synchronization signal from the illumination imaging synchronization unit 20, generates an image signal, and generates the generated image signal as an image distribution unit. 22 to send.
  • the image distribution unit 22 identifies the type of observation image to be formed based on the synchronization signal from the illumination imaging synchronization unit 20, and the image signal received from the imaging unit 18 in accordance with the identification result is used as the special light 1 image formation unit 24a, the special light image formation unit 24a.
  • the image is transmitted to a necessary image forming unit among the light 2 image forming unit 24b, the special light 3 image forming unit 24c, and the white light image forming unit 24d.
  • the image forming unit forms a corresponding observation image from the received image signal, and transmits the formed observation image to the image display unit 26.
  • the image display unit 26 displays the received observation image so that the user can easily see it. For example, as shown in FIG. 8, the image display unit 26 displays four observation images in parallel.
  • the observation image formed by the image forming unit is input from the image display unit 26 to the brightness correction unit 28.
  • the brightness correction unit 28 instructs the light source control unit 8 to correct the outputs of the lasers 1 to 7 so that the brightness of the observation image displayed on the image display unit 26 is appropriate.
  • FIG. 9 shows an example of laser output conditions when only the special light image 1 and the white light image are selected.
  • the two observation images are displayed in parallel as shown in FIG. In such an observation mode, it is only necessary to form two observation images in one frame. Therefore, as shown in FIG. 9, the lighting periods of the lasers 1, 4, 5, and 6 may be 1 ⁇ 2 period of one frame. Further, the laser 2 may be kept on.
  • the observation image formation period can be lengthened. Therefore, if the period of one frame is the same as that of the example of FIG. Can be long. Therefore, in the example of FIG. 9, it is possible to display a brighter observation image than in the example of FIG.
  • white light or special light is formed using a laser.
  • the laser can be easily introduced into a thin light guide member such as a fiber with high efficiency, and can realize illumination light with considerably higher brightness than an LED light source or a gas light source.
  • special light it is possible to acquire image information unique to only that wavelength compared to a light source having a broad spectrum such as an LED light source. Therefore, the image accuracy is high.
  • a white light image is constructed by utilizing a part of the special light laser, the number of lasers can be reduced and the cost and volume can be reduced. Further, since four white light image lasers are prepared, the color rendering property of the white light image is ensured. Furthermore, since the other laser is not turned on when acquiring the white light image, a white light image with high image accuracy can be formed. In addition, since a plurality of types of special light image lasers are also made common, the number of lasers can be reduced to reduce cost and volume.
  • the laser lighting start timing, the laser lighting period, and the laser lighting cycle corresponding to the observation mode in the observation mode storage unit 10 there is no useless driving of the laser. This can also reduce power consumption.
  • individually changing the lighting cycle of different lasers it is possible to keep the lasers lit across frames in which different image types are captured. This makes it possible to illuminate the shared laser without a load in terms of circuitry. This also makes it possible to reduce power consumption.
  • the illumination imaging synchronization unit 20 transfers an image signal to the image forming unit at an appropriate timing. This also makes it possible to reduce power consumption.
  • the medical image forming apparatus 100 of the present embodiment has a configuration in which a white light image is generated only by a laser prepared for a special light image, but this is not a limitation. In the case of a configuration in which a high-quality white light image cannot be created with only a laser prepared for a special light image, a white light image laser may be separately prepared.
  • the medical image forming apparatus 100 according to the present embodiment prepares different lasers for laser beams used for a plurality of types of special light. Also good. For example, the excitation center wavelength of porphyrin and the wavelength at which the oxide and hemoglobin-related spectra for hemoglobin match at 450 nm match. Therefore, the laser for forming the autofluorescence image and the laser for forming the oxygen saturation image may be only one 450 nm laser.
  • FIG. 11 is a block diagram showing a configuration of a medical image forming apparatus according to the second embodiment of the present invention.
  • the medical image forming apparatus 100 of this embodiment has a simpler configuration than that of the first embodiment. In the following, description of the configuration common to the first embodiment is omitted.
  • the medical image forming apparatus 100 of the second embodiment includes lasers 1 to 4 as illumination light sources.
  • laser 1 emits light with a wavelength of 400 nm
  • laser 2 emits light with a wavelength of 450 nm
  • laser 3 emits light with a wavelength of 540 nm
  • laser 4 emits light with a wavelength of 640 nm.
  • only two observation images of the special light image 1 (blood vessel emphasized image) and the white light image are formed at most. Therefore, there are only two image forming units.
  • FIG. 12 shows an example of laser output conditions when only the special light image 1 and the white light image are selected in the second embodiment.
  • the laser 1 and the laser 3 are turned on.
  • the laser 2, the laser 3, and the laser 4 are turned on during the white light image formation period.
  • the lighting cycle and the lighting period may be the same as those in FIG. In such a second embodiment, two observation images as shown in FIG. 13 are displayed in parallel.
  • the number of lasers and the number of other members can be further reduced as compared with the first embodiment.
  • individual functions can be simplified as compared with the first embodiment, it is possible to achieve cost reduction, volume reduction, and power consumption reduction as compared with the first embodiment.
  • the laser lighting period and the imaging period for one observation image are maximized within one frame. As a result, an image with high image accuracy can be acquired.

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